Method, system and storage medium for determining internal radiation dose rate for nuclide therapy

Abstract

The present application relates to the technical field of in vivo radiation dose rate determination, and specifically to a method, system, and storage medium for determining in vivo radiation dose rate during nuclide therapy. The method comprises: measuring an energy spectrum of radiation emitted from a body during nuclide therapy for a preset duration; collecting ambient temperature and humidity at each moment within the preset duration; analyzing deviations of ambient temperature at all moments from a preset standard temperature range, and ambient humidity at all moments from a preset standard humidity range, and correcting the radiation energy spectrum data; determining the characteristic complexity of the corrected radiation energy spectrum; obtaining an optimized path width of the radiation energy spectrum; and using the optimized path width to obtain an optimized radiation energy spectrum and obtain the in vivo radiation dose rate during nuclide therapy. This improves the accuracy of determining the in vivo radiation dose rate during nuclide therapy.

Description

Technical Field

[0001] The present application relates to the technical field of internal radiation dose rate determination, and in particular to a method, system and storage medium for determining internal radiation dose rate for radionuclide therapy. Background Art

[0002] After radionuclide therapy, residual radioactive elements remain in the patient's body, potentially causing radiation damage to medical workers and those in close contact with the patient. Therefore, measuring the radiation dose rate in patients after radionuclide therapy can provide a reference for the protection of medical and accompanying personnel and help guide subsequent treatment.

[0003] When conducting internal radiation dose rate testing, the radiation dose rate emitted from the patient's body is often measured. However, changes in environmental factors can easily cause The deviation of the X-ray energy spectrum data affects the Analysis of X-ray spectrum data, and During the analysis of X-ray energy spectrum data, setting the track width too large or too small will affect the distribution and overlap of the peaks, resulting in There are errors in the feature extraction of radiation energy spectrum data, which interferes with the determination of radiation dose rate in patients. Summary of the Invention

[0004] In order to solve the above technical problems, the purpose of this application is to provide a method, system and storage medium for determining the internal radiation dose rate of radionuclide therapy. The technical solutions adopted are as follows:

[0005] In a first aspect, an embodiment of the present application provides a method for determining an in vivo radiation dose rate for radionuclide therapy, the method comprising the following steps:

[0006] Measure the amount of radiation emitted from the body during nuclide treatment for a predetermined duration. Radiation energy spectrum; collecting ambient temperature and humidity at each moment within the preset time period;

[0007] Analyze the deviation of ambient temperature from the preset standard temperature range at all times, and the deviation of ambient humidity from the preset standard humidity range at all times, and Correct the data of the ray energy spectrum;

[0008] Based on the revised The overlap degree between each peak in the ray energy spectrum and its adjacent peaks is corrected. The degree of adjacent overlap of peaks in the ray energy spectrum;

[0009] Based on the correlation between the adjacent overlaps of all peaks, the adjacent overlaps of all peaks are divided into categories, and the corrected values ​​are obtained by comparing the differences between the adjacent overlaps of each category and the remaining categories. The intensive distribution coefficient of the ray energy spectrum, combined with the peak width of each peak, is used to obtain the corrected Characteristic complexity of the ray energy spectrum;

[0010] Based on the feature complexity, and The initial width of the ray energy spectrum is determined Optimize the channel width of the ray energy spectrum; use the optimized channel width to redistribute the channel number and calculate the corrected channel number. The counting information of the ray energy spectrum under the optimized path width is optimized X-ray energy spectrum;

[0011] Based on optimization The ray energy spectrum is used to calculate the activity of the radioactive source and determine the radiation dose rate in the body during radionuclide therapy;

[0012] Calculate the mean of the peak widths of each peak and its adjacent peaks, calculate the difference between the channel addresses of each peak and its adjacent peaks, record it as a third difference, calculate the ratio of the mean to the third difference, record it as a third ratio, and the adjacent overlap degree is the fusion result of the third ratios of each peak and all its adjacent peaks;

[0013] Calculate the difference between each adjacent overlap degree of each category and each adjacent overlap degree of any remaining category, record it as the fourth difference, and determine the average of all the fourth differences between each category and the any category as the inter-category difference coefficient between each category and the any category;

[0014] The dense distribution coefficient is the cumulative sum of the inter-class difference coefficients between any two classes;

[0015] Calculate the corrected The average value of the peak widths of all peaks in the ray energy spectrum, wherein the characteristic complexity is the ratio of the dense distribution coefficient to the average value;

[0016] The difference between the maximum and minimum track widths within the initial track width range is calculated, and a multiplication result of the difference and the normalized value of the feature complexity is calculated. The optimized track width is the difference between the maximum track width within the initial track width range and the multiplication result.

[0017] In one embodiment, the The data of the ray spectrum are corrected, including:

[0018] Analyze the situation where the ambient temperature at all times is lower than the preset standard temperature range, and the situation where the ambient humidity at all times is higher than the preset standard humidity range, and determine The first correction factor of the ray energy spectrum;

[0019] Analyze the situation where the ambient temperature at all times is higher than the preset standard temperature range, and the situation where the ambient humidity at all times is lower than the preset standard humidity range, and determine The second correction factor of the ray energy spectrum;

[0020] Combine the first correction coefficient and the second correction coefficient to The data of the X-ray energy spectrum are corrected.

[0021] In one embodiment, determining the first correction coefficient and the second correction coefficient includes:

[0022] Calculating the ratio of the number of ambient temperatures at all times that are lower than the preset standard temperature range to the total number of ambient temperatures at all times, recording this as a first ratio; calculating the difference between the minimum ambient temperature at all times and the lower limit of the preset standard temperature range, recording this as a first difference; and multiplying the first ratio by the first difference to determine the low temperature adjustment coefficient;

[0023] Calculate the ratio of the number of ambient humidity levels at all times that is higher than a preset standard humidity range to the total number of ambient humidity levels at all times, recording this as a second ratio; calculate the difference between the maximum ambient humidity at all times and an upper limit of the preset standard humidity range, recording this as a second difference; and multiply the second ratio by the second difference to determine the high humidity adjustment coefficient;

[0024] The first correction coefficient is a fusion result of the low temperature adjustment coefficient and the high humidity adjustment coefficient;

[0025] Using the high humidity adjustment coefficient calculation method, replace the ambient humidity with the ambient temperature to determine the high temperature adjustment coefficient; using the low temperature adjustment coefficient calculation method, replace the ambient temperature with the ambient humidity to determine the low humidity adjustment coefficient;

[0026] The second correction coefficient is a fusion result of the high temperature adjustment coefficient and the low humidity adjustment coefficient.

[0027] In one embodiment, the first correction coefficient and the second correction coefficient are combined to The data of the ray spectrum are corrected, including:

[0028] The difference between the first correction coefficient and the second correction coefficient is mapped into a preset range, and the value mapped into the preset range is recorded as B. Then the corrected X-ray spectrum data The calculation method is: ;in, Before correction X-ray spectrum data.

[0029] In a second aspect, an embodiment of the present application also provides a system for determining the in vivo radiation dose rate of radionuclide therapy, comprising a memory, a processor, and a computer program stored in the memory and running on the processor, wherein the processor implements the steps of any one of the above-mentioned methods when executing the computer program.

[0030] In a third aspect, an embodiment of the present application further provides a storage medium for determining the in vivo radiation dose rate of radionuclide therapy, wherein the medium stores a computer program, and when the computer program is executed by a processor, it implements any of the above-mentioned methods for determining the in vivo radiation dose rate of radionuclide therapy.

[0031] This application has at least the following beneficial effects:

[0032] The present invention measures the emission of radioactive substances in vivo during the treatment of nucleoside for a predetermined period of time. Ray energy spectrum; collecting the ambient temperature and humidity at each moment within the preset time; analyzing the deviation of the ambient temperature at all times from the preset standard temperature range, and the deviation of the ambient humidity at all times from the preset standard humidity range, Correct the data of the ray energy spectrum; avoid the influence of ambient temperature and humidity on The interference of X-ray spectrum data improves The accuracy and reliability of X-ray spectrum data; based on the corrected The overlap degree between each peak in the ray energy spectrum and its adjacent peaks is corrected. The adjacent overlap degree of each peak in the X-ray energy spectrum reflects the degree of overlap between each peak and its adjacent peak, which reflects the The suitability of the channel width and channel number set when spectrally analyzing the X-ray energy spectrum. The greater the adjacent overlap, the higher the overlap between peaks. The peaks cannot be effectively separated. The lower the suitability of the channel width and channel number set when spectrally analyzing the ray energy spectrum; further, based on the correlation between the adjacent overlaps of all peaks, the adjacent overlaps of all peaks are divided into categories, and the corrected values ​​are obtained by comparing the adjacent overlaps of each category with the remaining categories. The intensive distribution coefficient of the ray energy spectrum, combined with the peak width of each peak, is used to obtain the corrected The characteristic complexity of the ray energy spectrum; the characteristic complexity reflects the corrected The density of peak positions in the local range of the ray energy spectrum improves the The accuracy of optimizing the width of the ray spectrum; based on the feature complexity, and The initial width of the ray energy spectrum is determined Optimized path width of the ray energy spectrum; using the optimized path width, the optimized Radiation energy spectrum, obtain the radiation dose rate of the body during radionuclide therapy, and eliminate the influence of environmental factors on the radiation dose. The deviation caused by the X-ray spectrum data improves The accuracy of the optimized width setting of the ray energy spectrum further improves the optimization The reliability of the radiation energy spectrum improves the accuracy of determining the radiation dose rate in the body during radionuclide therapy. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] In order to more clearly illustrate the technical solutions and advantages of the embodiments of the present application or the prior art, the following is a brief introduction to the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work.

[0034] Figure 1 A flowchart of a method for determining an in vivo radiation dose rate for radionuclide therapy provided in one embodiment of the present application;

[0035] Figure 2 Flowchart for internal radiation dose rate determination. DETAILED DESCRIPTION

[0036] To further illustrate the technical means and effectiveness of this application to achieve its intended purpose, the following, in conjunction with the accompanying drawings and preferred embodiments, details the specific implementation, structure, features, and effectiveness of a method, system, and storage medium for determining the internal radiation dose rate for radionuclide therapy proposed in this application. In the following description, references to different "one embodiment" or "another embodiment" do not necessarily refer to the same embodiment. Furthermore, specific features, structures, or characteristics of one or more embodiments may be combined in any suitable manner.

[0037] Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs.

[0038] The following describes in detail a method, system and storage medium for determining the in vivo radiation dose rate of radionuclide therapy provided by the present application with reference to the accompanying drawings.

[0039] See also Figure 1 , which shows a flowchart of a method for determining an in vivo radiation dose rate of radionuclide therapy provided by one embodiment of the present application, the method comprising the following steps:

[0040] S1 measures the amount of radiation emitted from the body during nuclide treatment for a preset duration. Radiation energy spectrum; collecting the ambient temperature and humidity at each moment within the preset time period.

[0041] This embodiment uses a high-purity germanium detector to directly measure the radiation emitted by radioactive substances in the human body from outside the human body. The main function of the high purity germanium detector is to transmit the radiation emitted by radioactive nuclides. The radiation is converted into a measurable electrical signal, and then the signal amplifier is used to amplify the electrical signal measured by the detector, and then the analog-to-digital converter is used to convert the amplified electrical signal into a digital signal. Finally, a multi-channel analyzer is used to perform energy spectrum analysis on the digital signal to obtain the energy spectrum within the preset time. X-ray energy spectrum, in In the ray energy spectrum, the horizontal axis represents each energy range, and the vertical axis represents the radiation detected by the detector in each energy range. The number of ray events; where The determination of the ray energy spectrum is a well-known technology, and the specific process will not be described in detail. During the preset time of the ray energy spectrum, the temperature sensor and humidity sensor are used to measure the ambient temperature and humidity at each moment in the same space.

[0042] It should be noted that the preset duration in this embodiment is 2 minutes, the ambient temperature and ambient humidity are collected synchronously, and the collection time interval is 1 second. The implementers can set the preset duration and collection time interval according to actual conditions, and this embodiment does not limit this.

[0043] S2, analyzing the deviation of the ambient temperature from the preset standard temperature range at all times, and the deviation of the ambient humidity from the preset standard humidity range at all times, and The data of the X-ray energy spectrum are corrected.

[0044] exist During the detection of radiation, the temperature and humidity of the environment may interfere with the acquired energy spectrum data. Specifically, changes in temperature and humidity will affect the gain setting of the detector, which will cause the energy spectrum data to shift up and down, and ultimately The peak shapes in the X-ray energy spectrum change, which in turn affects the subsequent energy spectrum analysis. Therefore, it is necessary to adjust the The X-ray energy spectrum data is corrected.

[0045] Affected by the hospital ventilation system, personnel activities and climatic conditions, it is easy to cause temperature and humidity changes, affecting the propagation and attenuation characteristics of the radiation signal, as well as The performance of the X-ray spectrum measuring instrument will have a certain impact on the accuracy of the spectrum data. For example, the scintillator and photomultiplier tube in the detector have temperature effects. As the temperature rises or falls, the luminous efficiency, photoelectric conversion efficiency and other parameters of these components will change, thus affecting the amplitude of the electrical pulse. When the temperature rises, the luminous efficiency and photoelectric conversion efficiency of these components will change. The measured peak position in the ray energy spectrum will shift to the left, and the counting rate will increase to a certain extent, causing the energy spectrum data to shift upward, that is, the data is too high. When the temperature drops, the peak position will shift to the right, and the counting rate will decrease relatively. When the humidity is high, the water molecules in the air will increase. These water molecules may have a certain absorption and scattering effect on the radiation signal, causing the detected energy spectrum data to shift downward, that is, the data is too low. In this embodiment, the temperature range under the standard detection state is set to The humidity range under standard detection conditions is 30% to 75%. If the current temperature and humidity conditions deviate from the standard detection conditions, the resulting energy spectrum data will be more offset. Therefore, this embodiment corrects the obtained energy spectrum data based on the deviation of the collected temperature and humidity data from the standard temperature and humidity range.

[0046] First, the ratio of the number of ambient temperatures at all times that are lower than the preset standard temperature range to the total number of ambient temperatures at all times is calculated, recorded as a first ratio. The difference between the minimum ambient temperature at all times and the lower limit of the preset standard temperature range is calculated, recorded as a first difference. The product of the first ratio and the first difference is determined as the low temperature adjustment coefficient.

[0047] Calculate the ratio of the number of ambient humidity levels at all times that is higher than a preset standard humidity range to the total number of ambient humidity levels at all times, recording this as a second ratio; calculate the difference between the maximum ambient humidity at all times and an upper limit of the preset standard humidity range, recording this as a second difference; and multiply the second ratio by the second difference to determine the high humidity adjustment coefficient;

[0048] The fusion result of the low temperature adjustment coefficient and the high humidity adjustment coefficient is determined as The first correction factor of the X-ray energy spectrum.

[0049] It should be noted that the difference represents the degree of difference between two variables, which can be calculated by the absolute value of the difference, the square of the difference, the ratio, etc. In this embodiment, the difference is calculated by the absolute value of the difference; fusion represents the combination of two variables, which can be calculated by addition, multiplication, a mixture of addition and multiplication, and averaging.

[0050] In this embodiment, the sum of the low temperature adjustment coefficient and the high humidity adjustment coefficient is determined as The first correction factor of the X-ray energy spectrum.

[0051] It should be understood that when the temperature is low or the humidity is high, the energy spectrum data measured will be high, and the greater the deviation from the standard temperature and humidity range, the greater the deviation of the energy spectrum data. The greater the degree to which the X-ray energy spectrum data is biased, the greater the bias may be.

[0052] In addition, when the temperature is too high or the humidity is too low, the measured energy spectrum data will be too low, and the greater the deviation from the standard temperature and humidity range, the greater the deviation of the energy spectrum data. Therefore, this embodiment adopts the calculation method of the high humidity adjustment coefficient, replaces the ambient humidity with the ambient temperature, and records the calculated result as the high temperature adjustment coefficient. The calculation method of the low temperature adjustment coefficient is adopted, replaces the ambient temperature with the ambient humidity, and records the calculated result as the low humidity adjustment coefficient. The sum of the high temperature adjustment coefficient and the low humidity adjustment coefficient is used as The second correction coefficient of the X-ray energy spectrum. The larger the second correction coefficient, the more likely the measured energy spectrum data is to be underestimated.

[0053] It should be noted that the energy spectrum data involved in this embodiment is The vertical axis value in the X-ray energy spectrum.

[0054] Furthermore, the energy spectrum data is corrected according to the first correction coefficient and the second correction coefficient. Specifically, the difference between the second correction coefficient and the first correction coefficient is recorded as A. If A is a positive value, it indicates that the energy spectrum data is too low and needs to be amplified and corrected. If A is a negative value, it indicates that the energy spectrum data is too high and needs to be reduced and corrected. If A is 0, it indicates that the energy spectrum data does not need to be corrected. The degree of deviation of the radiation dose rate caused by temperature and humidity changes is usually in the range of Therefore, A is scaled and mapped to control the size of A within the range of (-0.1, 0.1), and the value of A mapped to the range of (-0.1, 0.1) is recorded as B. X-ray spectrum data The calculation method is: ;in, Before correction X-ray spectrum data.

[0055] So far, the correction processing of energy spectrum data has been realized, which can reduce the impact of environmental changes on energy spectrum analysis to a certain extent. The corrected energy spectrum data reduces the data offset and improves The accuracy of peak shape and peak position information in the X-ray energy spectrum. Since the channel width and number of channels of the multi-channel analyzer need to be selected according to the complexity of the energy spectrum during energy spectrum analysis, more accurate energy spectrum data can improve the accuracy of determining the channel width and number of channels when performing energy spectrum analysis on the multi-channel analyzer.

[0056] S3, based on the revised The overlap degree between each peak in the ray energy spectrum and its adjacent peaks is corrected. The degree of adjacent overlap of peaks in the X-ray energy spectrum.

[0057] In the process of classification and statistics of multi-channel analyzers, selecting the appropriate number of channels and channel width is a key step to achieve accurate measurement and analysis. The channel width refers to the energy range covered by each channel, and the number of channels refers to the total number of channels that the multi-channel analyzer can be divided into. The complex characteristics of the X-ray energy spectrum are reflected in the degree of overlap between peaks, the density of peak distribution and the difference in peak shape. If the X-ray energy spectrum has many narrow peaks and overlapping peaks with similar energies, a higher energy resolution is required. Accordingly, more channels and smaller channel widths need to be set to distinguish these peaks to ensure that each peak can cover enough channels, thereby improving the accuracy of the activity calculation of the radioactive source.

[0058] During the radiation dose rate detection process, due to background radiation interference and the nuclide decay process, multiple radiation with similar energy may be generated. Radiation can easily lead to Overlapping peaks are formed in the energy spectrum of the radiation, and under the influence of multiple radionuclides, the peak shape may be narrow and the peaks may be densely distributed in a local area, thereby interfering with the accuracy of the multi-channel analyzer in identifying the energy spectrum characteristics.

[0059] Therefore, for analysis The overlapping distribution characteristics of the ray energy spectrum are firstly analyzed by a polynomial fitting method. The energy spectrum of the ray is fitted to obtain the corresponding fitting curve, and then all peak points in the fitting curve are further obtained by the derivative peak search method, where each peak point corresponds to A peak in the ray energy spectrum, and then identify The peaks in the X-ray energy spectrum.

[0060] by Taking the i-th peak in the X-ray energy spectrum as an example, first obtain the overlapping characteristics between the i-th peak and the next adjacent peak, calculate the absolute value of the difference in the corresponding address between the i-th peak and the i+1-th peak, record it as the third difference, then calculate the average of the peak widths corresponding to the i-th peak and the i+1-th peak, and use the ratio of the average of the peak widths to the third difference as the overlapping coefficient between the i-th peak and the i+1-th peak, record it as the third ratio. If the distance between the peak points is smaller and the adjacent peak widths are larger, it means that the degree of overlap between the i-th peak and the i+1-th peak is greater, and the resulting overlapping coefficient is also larger. For the i-th peak and the i-1-th peak, the same calculation steps as the i-th peak and the i+1-th peak are used to obtain the overlapping coefficient between the i-th peak and the i-1-th peak, and then use the average of the overlapping coefficients between the i-th peak and the i+1-th peak and the i-1-th peak as the adjacent overlapping degree of the i-th peak. The larger the adjacent overlapping degree obtained, the greater the overlap. The greater the degree of overlap of the i-th peak in the ray energy spectrum.

[0061] S4, based on the correlation between the adjacent overlaps of all peaks, the adjacent overlaps of all peaks are divided into categories, and the corrected adjacent overlaps are obtained by comparing the differences between each category and the remaining categories. The intensive distribution coefficient of the ray energy spectrum, combined with the peak width of each peak, is used to obtain the corrected Characteristic complexity of the ray energy spectrum.

[0062] Further, for analysis Whether there is a dense distribution feature of peak points in the local range in the ray energy spectrum, this embodiment uses the density peak clustering algorithm to cluster the adjacent overlap of all peak points, and outputs them as clusters, recorded as categories, and the data in the clusters are the adjacent overlap corresponding to each peak. The peak points of the ray energy spectrum are densely distributed in a local range, and the data differences between the obtained clusters will be significantly larger. Therefore, taking the kth cluster and the hth cluster as examples, the absolute value of the difference between each adjacent overlap degree in the kth cluster and each adjacent overlap degree in the hth cluster is calculated, recorded as the fourth difference, and the mean of all the fourth differences between the kth cluster and the hth cluster is used as the inter-class difference coefficient between the kth cluster and the hth cluster, that is, the inter-class difference coefficient between the kth category and the hth category. The larger the inter-class difference coefficient obtained, the greater the difference in the degree of overlap of the corresponding peaks between the kth cluster and the hth cluster. The sum of the inter-class difference coefficients between all any two clusters is taken as the corrected The intensive distribution coefficient of the ray energy spectrum is recorded as E. The larger E is, the The more likely it is that there will be a dense distribution of peaks in a local area in the ray energy spectrum.

[0063] Further considerations The width of all peaks in the X-ray energy spectrum is calculated after correction The average of the peak widths of all peaks in the X-ray energy spectrum is calculated by comparing E with the corrected The ratio of the average peak widths of all peaks in the X-ray spectrum is used as the corrected The characteristic complexity of the ray energy spectrum is recorded as F. The larger F is, the The greater the complexity of the X-ray energy spectrum, the higher the peak density. During the classification and statistics process of the multi-channel analyzer, a smaller channel width and more channels should be set to divide the peak positions more accurately.

[0064] S5, based on the feature complexity, and The initial width of the ray energy spectrum is determined Optimized path width of the ray energy spectrum; using the optimized path width, the optimized Ray energy spectrum, to obtain the radiation dose rate in the body of radionuclide therapy.

[0065] This embodiment uses the Sigmoid function to obtain the corrected The normalized value of the characteristic complexity of the ray energy spectrum can be selected by the implementer from other feasible normalization methods, which is not limited in this embodiment. The energy distribution range of the ray and the energy resolution of the detector are used to obtain the initial track width range. The acquisition of the initial track width range is a well-known technique. Therefore, this embodiment determines the initial track width range based on the normalized value. The optimized path width of the ray energy spectrum is calculated as follows: , where W is Optimized path width of the ray energy spectrum, is the maximum track width in the initial track width range, It represents the difference between the maximum and minimum track widths within the initial track width range, and G is the corrected The normalized value of the characteristic complexity of the ray energy spectrum can then be calculated based on the measurement range of the detector and The multi-channel analyzer calculates the corrected channel number based on the optimized channel width and channel number. The ray energy spectrum is re-counted and optimized Radiation energy spectrum. Helps improve the efficiency and accuracy of radiation dose rate determination.

[0066] Based on optimization The activity of the radioactive source is calculated based on the energy spectrum of the ray, and the radiation dose rate is determined based on the activity of the radioactive source. Calculating the activity of the radiation source using the energy spectrum and determining the radiation dose rate based on the activity of the radiation source are both existing well-known technologies, and the specific process will not be described in detail. The flow chart for determining the radiation dose rate in the body is as follows: Figure 2 shown.

[0067] Based on the same inventive concept as the above-mentioned method, an embodiment of the present application also provides a system for determining the in vivo radiation dose rate of radionuclide therapy, comprising a memory, a processor, and a computer program stored in the memory and running on the processor. When the processor executes the computer program, the steps of any one of the above-mentioned methods for determining the in vivo radiation dose rate of radionuclide therapy are implemented.

[0068] Based on the same inventive concept as the above method, an embodiment of the present application also provides a storage medium for determining the in vivo radiation dose rate of radionuclide therapy, wherein the medium stores a computer program, and when the computer program is executed by a processor, it implements any of the above methods for determining the in vivo radiation dose rate of radionuclide therapy.

[0069] It should be noted that the order in which the embodiments of the present application are presented is for illustrative purposes only and does not necessarily represent the superiority or inferiority of the embodiments. Furthermore, the foregoing descriptions of specific embodiments of this specification are provided. Furthermore, the processes depicted in the accompanying drawings do not necessarily require the specific order or sequential sequence shown to achieve the desired results. In certain embodiments, multitasking and parallel processing are also possible or may be advantageous.

[0070] The various embodiments in this specification are described in a progressive manner, and the same or similar parts between the various embodiments can be referred to each other. Each embodiment focuses on the differences from other embodiments.

[0071] The above description is only a preferred embodiment of the present application and is not intended to limit the present application. Any modifications, equivalent replacements, improvements, etc. made within the principles of the present application shall be included in the scope of protection of the present application.

Claims

1. A method for determining the internal radiation dose rate of radionuclide therapy, characterized in that: The method comprises the following steps: Measure the amount of radiation emitted from the body during nuclide treatment for a predetermined duration. Radiation energy spectrum; collecting ambient temperature and humidity at each moment within the preset time period; Analyze the deviation of ambient temperature from the preset standard temperature range at all times, and the deviation of ambient humidity from the preset standard humidity range at all times, and Correct the data of the ray energy spectrum; Based on the revised The overlap degree between each peak in the ray energy spectrum and its adjacent peaks is corrected. The degree of adjacent overlap of peaks in the ray energy spectrum; Based on the correlation between the adjacent overlaps of all peaks, the adjacent overlaps of all peaks are divided into categories, and the corrected values ​​are obtained by comparing the differences between the adjacent overlaps of each category and the remaining categories. The intensive distribution coefficient of the ray energy spectrum, combined with the peak width of each peak, is used to obtain the corrected Characteristic complexity of the ray energy spectrum; Based on the feature complexity, and The initial width of the ray energy spectrum is determined Optimize the channel width of the ray energy spectrum; use the optimized channel width to redistribute the channel number and calculate the corrected channel number. The counting information of the ray energy spectrum under the optimized path width is optimized X-ray energy spectrum; Based on optimization The ray energy spectrum is used to calculate the activity of the radioactive source and determine the radiation dose rate in the body during radionuclide therapy; Calculate the mean of the peak widths of each peak and its adjacent peaks, calculate the difference between the channel addresses of each peak and its adjacent peaks, record it as a third difference, calculate the ratio of the mean to the third difference, record it as a third ratio, and the adjacent overlap degree is the fusion result of the third ratios of each peak and all its adjacent peaks; Calculate the difference between each adjacent overlap degree of each category and each adjacent overlap degree of any remaining category, record it as the fourth difference, and determine the average of all the fourth differences between each category and the any category as the inter-category difference coefficient between each category and the any category; The dense distribution coefficient is the cumulative sum of the inter-class difference coefficients between any two classes; Calculate the corrected The average value of the peak widths of all peaks in the ray energy spectrum, wherein the characteristic complexity is the ratio of the dense distribution coefficient to the average value; The difference between the maximum and minimum track widths within the initial track width range is calculated, and a multiplication result of the difference and the normalized value of the feature complexity is calculated. The optimized track width is the difference between the maximum track width within the initial track width range and the multiplication result.

2. The method for determining the internal radiation dose rate of nuclide therapy according to claim 1, wherein: The pair The data of the ray spectrum are corrected, including: Analyze the situation where the ambient temperature at all times is lower than the preset standard temperature range, and the situation where the ambient humidity at all times is higher than the preset standard humidity range, and determine The first correction factor of the ray energy spectrum; Analyze the situation where the ambient temperature at all times is higher than the preset standard temperature range, and the situation where the ambient humidity at all times is lower than the preset standard humidity range, and determine The second correction factor of the ray energy spectrum; Combine the first correction coefficient and the second correction coefficient to The data of the X-ray energy spectrum are corrected.

3. The method for determining the internal radiation dose rate of nuclide therapy according to claim 2, wherein: Determining the first correction coefficient and the second correction coefficient includes: Calculating the ratio of the number of ambient temperatures at all times that are lower than the preset standard temperature range to the total number of ambient temperatures at all times, recording this as a first ratio; calculating the difference between the minimum ambient temperature at all times and the lower limit of the preset standard temperature range, recording this as a first difference; and multiplying the first ratio by the first difference to determine the low temperature adjustment coefficient; Calculate the ratio of the number of ambient humidity levels at all times that is higher than a preset standard humidity range to the total number of ambient humidity levels at all times, recording this as a second ratio; calculate the difference between the maximum ambient humidity at all times and an upper limit of the preset standard humidity range, recording this as a second difference; and multiply the second ratio by the second difference to determine the high humidity adjustment coefficient; The first correction coefficient is a fusion result of the low temperature adjustment coefficient and the high humidity adjustment coefficient; Using the high humidity adjustment coefficient calculation method, replace the ambient humidity with the ambient temperature to determine the high temperature adjustment coefficient; using the low temperature adjustment coefficient calculation method, replace the ambient temperature with the ambient humidity to determine the low humidity adjustment coefficient; The second correction coefficient is a fusion result of the high temperature adjustment coefficient and the low humidity adjustment coefficient.

4. The method for determining the internal radiation dose rate of nuclide therapy according to claim 3, wherein: The combination of the first correction coefficient and the second correction coefficient is The data of the ray spectrum are corrected, including: The difference between the first correction coefficient and the second correction coefficient is mapped into a preset range, and the value mapped into the preset range is recorded as B. Then the corrected X-ray spectrum data The calculation method is: ;in, Before correction X-ray spectrum data.

5. A system for determining an in vivo radiation dose rate for nuclide therapy, applied to a method for determining an in vivo radiation dose rate for nuclide therapy according to claim 1, characterized in that: The system includes a memory, a processor, and a computer program stored in the memory and running on the processor. When the processor executes the computer program, the steps of the method according to any one of claims 1 to 4 are implemented.

6. A storage medium for determining an in vivo radiation dose rate for radionuclide therapy, wherein a computer program is stored in the medium, characterized in that: When the computer program is executed by a processor, the method for determining the in vivo radiation dose rate of nuclide therapy according to any one of claims 1 to 4 is implemented.

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